WO1999044547A1 - Lower limb prosthesis and control unit - Google Patents
Lower limb prosthesis and control unit Download PDFInfo
- Publication number
- WO1999044547A1 WO1999044547A1 PCT/GB1999/000640 GB9900640W WO9944547A1 WO 1999044547 A1 WO1999044547 A1 WO 1999044547A1 GB 9900640 W GB9900640 W GB 9900640W WO 9944547 A1 WO9944547 A1 WO 9944547A1
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- variability
- locomotion
- prosthesis
- parameter
- control device
- Prior art date
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/50—Prostheses not implantable in the body
- A61F2/68—Operating or control means
- A61F2/70—Operating or control means electrical
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/50—Prostheses not implantable in the body
- A61F2/68—Operating or control means
- A61F2/74—Operating or control means fluid, i.e. hydraulic or pneumatic
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/50—Prostheses not implantable in the body
- A61F2/60—Artificial legs or feet or parts thereof
- A61F2/64—Knee joints
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/50—Prostheses not implantable in the body
- A61F2/78—Means for protecting prostheses or for attaching them to the body, e.g. bandages, harnesses, straps, or stockings for the limb stump
- A61F2/80—Sockets, e.g. of suction type
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/50—Prostheses not implantable in the body
- A61F2002/5003—Prostheses not implantable in the body having damping means, e.g. shock absorbers
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/50—Prostheses not implantable in the body
- A61F2/60—Artificial legs or feet or parts thereof
- A61F2002/607—Lower legs
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/50—Prostheses not implantable in the body
- A61F2/68—Operating or control means
- A61F2/70—Operating or control means electrical
- A61F2002/704—Operating or control means electrical computer-controlled, e.g. robotic control
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/50—Prostheses not implantable in the body
- A61F2/68—Operating or control means
- A61F2/70—Operating or control means electrical
- A61F2002/705—Electromagnetic data transfer
Definitions
- This invention relates to a lower limb prosthesis including a dynamically adjustable joint movement control unit arranged to control either or both of flexion and extension of the joint automatically.
- a pneumatic piston and cylinder device coupled between the thigh part and the shin part has a motor-driven valve which alters the resistance of the device to movement at the knee joint in response to command signals from an electronic control circuit deriving input signals from a transducer mounted on the control device, the repetition rate of the input signals being representative of the speed of locomotion, particularly the step period during walking.
- the control circuit includes a radio receiver for receiving command signals from a remote control transmitter operated by a prosthetist, a processor for processing the command signals and the transducer signals, and a memory for storing a map of valve settings against locomotion speed ranges.
- the processor has a teaching mode whereby the amputee is asked to walk at a particular speed and the system is "taught" by the prosthetist inasmuch as the prosthetist causes the valve to be adjusted under remote control in real time while the amputee is walking until the best gait is obtained. The same process is performed at different walking speeds and the prosthetist selects a valve setting for each speed which, in his or her opinion, appears to produce the best walking gait. These valve settings are stored at the end of a teaching session. In a playback mode of the processor, signals corresponding to the stored valve settings are fed to the motor-driven valve automatically according to the speed at which the amputee walks.
- the above system has yielded notable improvements in gait for above-knee amputees due to its adaptation of resistance to knee joint movement to different settings suiting different walking speeds rather than relying on a fixed resistance setting for all walking speeds. These improvements have been achieved without requiring excessively lengthy sessions with the prosthetist.
- a lower limb prosthesis which automatically reacts to a variability measurement dynamically to adjust a control device which forms part of the prosthesis and which affects the flexion and/or the extension of a joint connecting different parts of the prosthesis.
- a self -learning adaptive control system for a lower limb prosthesis, the system measuring the variation of one or more parameters associated with the dynamic operation of the limb, and automatically processing the variation measurement to optimise or reduce the variability of the parameter, preferably using an iterative process, in order to achieve an optimum locomotion characteristic.
- the system is primarily applicable to a lower limb prosthesis for an above-knee amputee, the control device being a knee flexion control device such as a piston and cylinder assembly having an electrically adjustable valve responsive to an adjusting signal generated by a microprocessor which is programmed to derive a kinematic parameter variability value from input signals produced by a transducer mounted on the limb.
- the kinematic parameter may be the amplitude of the flexion angle of the joint which, in the case of flexion and/or extension of the joint being controlled by a piston and cylinder device connected between a side part and a shin part of the prosthesis, may be represented by the amplitude or magnitude of the piston stroke.
- the duration of the flexed state may be used as another kinematic parameter, preferably as a proportion of the total step period.
- stride length may be used as a kinematic parameter.
- a lower limb prosthesis for an above-knee amputee including a dynamically adjustable knee movement control unit arranged to control flexion and/or extension of a knee joint of the prosthesis automatically in response to the sensed variability of at least one kinetic or kinematic parameter of locomotion in order to reduce the said variability.
- the sensed variability is an electrical signal value representative of the degree of variation of a kinematic parameter measured during each of a plurality of steps taken by the amputee during locomotion, the parameter being measured during each step taken by the amputee which is within a predetermined range of locomotion, such as a particular walking speed range or a particular category of locomotion.
- categories of locomotion means different modes of locomotion such as walking on a level surface, walking down an incline, walking up an incline, walking down stairs, climbing up stairs, or running.
- Speeds of walking or running as speed ranges may be determined by measuring the repetition rate or the average step period of a walking or running cycle, each cycle extending, for instance, from heel contact to heel contact through stance phase and swing phase.
- the control system may be configured to determine the variability of one or more kinetic or kinematic parameters over each of a plurality of the ranges of locomotion so that the control device is adjusted to a plurality of optimum settings for the different respective locomotion ranges. It is possible, then, for the system to determine the range of locomotion from received electrical signals from one or more transducers forming part of the prosthesis, and, using the same signals, to perform an iterative variability measurement and adjustment process within each respective locomotion range. The process minimises variability of the selected parameter or, in the case of the variability a plurality of parameters being measured, minimises the variability of at least one of them (which is designated the primary parameter).
- altering or minimising the variability of a kinematic parameter is associated with altering or minimising an underlying kinetic parameter of locomotion.
- a lower limb prosthesis includes a dynamically adjustable control device for controlling movement of the prosthesis during locomotion, a transducer for generating a sensing signal related to a kinematic parameter of locomotion, and an electronic control circuit having an input coupled to the transducer and an output coupled to the control device, wherein the transducer and the control circuit are configured to determine the variability of the kinematic parameter and to generate output signals for adjusting the control device thereby to reduce the variability of the parameter.
- control circuit is configured to record a value of the kinematic parameter during each of a plurality of locomotion cycles, to compare the recorded values to a establish a variability measurement, to compare the variability measurement with a reference variability value and, if the variability measurement exceeds the reference value, to initiate a control device adjustment procedure in which the control device is dynamically adjusted so as substantially to minimise the variability of the or each parameter.
- the preferred control system measures the speed of walking, computes the variation of a kinematic parameter over a number of steps, processes the measured parameter data in order to determine whether the degree of variation falls within a band of optimum parameter variation, adjusts the resistance to joint flexion and/or extension by a predetermined increment in accordance with the degree of variation of the parameter or parameters in order to reduce the amount of variability.
- the corresponding control device settings, in conjunction with walking speed values, can be stored in order that, in a playback mode, the control device is adjusted to a variability-minimising setting corresponding to a measured walking speed as determined by the stored relationships.
- the optimisation process may be carried out continuously during use of the prosthesis, variation of the kinematic parameters being iteratively reduced whenever the variability deviates from a predetermined optimum condition.
- the speed of walking may be defined according to a number of non-overlapping speed ranges which might be designated "slow",
- Figure 1 is a partly sectioned side elevation of part of a lower limb prosthesis incorporating a flexion control device and electronic control elements;
- FIG. 2 is a block diagram of a prosthesis control system in accordance with the invention.
- FIG. 3 is a flow chart illustrating a preferred sequence of operations performed by the control system.
- FIG. 1 A lower limb prosthesis in accordance with the invention is shown in Figure 1.
- the prosthesis has a knee joint 10 with a knee pivot 12 connecting a thigh component 14 to a shin component 16.
- the thigh component comprises a knee chassis 14A, an alignment device 14B, and a stump socket 14C.
- the shin component 16 has a conventional carbon fibre reinforced plastics shin cradle 16A which houses a piston and cylinder assembly 18 acting as a flexion control device to form part of a control system.
- the assembly 18 comprises a cylinder 18A which is pivotally coupled to the posterior part of the shin cradle 16 A, and a piston 18B having a piston rod 18C which is pivotally coupled to the knee chassis 14 A.
- the piston and cylinder assembly 18 is a pneumatic device, the resistance to flexion of the knee joint being controlled by a needle valve 18D which is adjustable by an electrical stepper motor 20 and an associated screw-threaded shaft 20A connected to the needle member of the needle valve.
- a d.c. motor may be used as an alternative to a stepper motor.
- the needle valve 18D lies in a passage 18E in the body of the cylinder 18 A, the passage 18E interconnecting the cylinder interior spaces 18F, 18G on opposite sides of the piston 18C and emerging at a port 18H in the wall of the cylinder. Operation of the motor 20 causes the shaft 20A to move axially so that the needle member moves into or out of a passageway forming part of passage 18E.
- the passage 18E constitutes a first bypass passage interconnecting the cylinder spaces on opposite sides of the piston 18C.
- a second bypass passage 181 incorporating a valve such as a one-way valve 18J is formed in the piston 18C so that the needle valve 18D is effective only on one stroke of the piston, in this case the stroke corresponding to increasing flexion of the knee joint 10.
- the one-way valve 18J may be arranged so as not to close-off the second bypass passage 181 completely on the increasing flexion stroke, but rather merely to reduce the orifice area through the piston 18C.
- Such an arrangement has the effect of the needle valve 18D determining the resistance to motion of the piston 18C in both directions, i.e. for increasing and decreasing flexion, but with the effect of variations in the orifice area of the needle valve 18D being greater in one direction than the other, depending on the direction of operation of the valve 18J.
- stepper motor 20 and its threaded shaft 20 A are mounted in the body of the cylinder 18, preferably adjacent the pivotal coupling 21 of the cylinder 18 to the shin 16.
- the stepper motor is driven by a microcomputer which forms part of an electronic circuit assembly 22 and is part of the control system.
- the microcomputer determines knee flexion and extension movements by means of a magnetic proximity sensor comprising a first part, preferably a transducer 24A, mounted in or associated with the cylinder body 18 A, and a second part, preferably a permanent magnet 24B, mounted on or associated with the piston
- transducer 24 A may be mounted on a printed circuit board constituting the electronic circuit assembly 22 which is, in turn, associated with cylinder 18.
- the electronic circuit assembly 22 and the stepper motor 20 are powered by batteries, one of which is shown in Figure 1 and indicated by the reference 26.
- the electronic circuit assembly 22 is shown in more detail in Figure 2. More particularly, the circuitry comprises a processor circuit 32 which receives transducer signals via input 34 and controls the stepper motor 20 via output 36.
- a non-volatile memory in the form of an EEPROM 38 stores walking speed and valve setting data produced by the processor circuit
- the processor circuit 32 includes an output driver for driving the stepper motor 20 which in turn moves the needle valve 18D, and it has an input for receiving signals from the flexion sensor 24 comprising transducer 24 A and magnet 24B (See Figure 1).
- This program offers automatic setting of the control device valve ("automatic programming") without intervention by a prosthetist, but manual programming by the prosthetist using a remote control unit as described in the above-mentioned British Patent Application No. 2280609A can be performed as an alternative to or in conjunction with automatic programming using additional software stored in the electronic circuitry 22.
- the signals received from transducer 24A can be interpreted by measuring their width, magnitude, and repetition rate to derive values for the step period (the reciprocal of the walking speed), the stroke magnitude, and stroke duration, the last of these being representative of the time taken to complete the swing phase relative to the complete step period.
- These three variables are designated T, ISI, and T s in Figure 3.
- the stroke magnitude and stroke duration are kinematic parameters, the variability of which is assessed in order to obtain an optimum setting of the swing phase resistance offered by piston and cylinder assembly 18 in each of five different walking speed ranges (represented in Figure 3 by step period ranges Ti to T 5 >. Different numbers of walking speed ranges may be used.
- the variability measurements ⁇ lSI and ⁇ T S are determined by comparing the stroke magnitude and stroke duration measurements over a number of consecutive steps, here seven steps, for which T remains within one of the ranges Ti to T 5 . According to whether these variability values ⁇ lSI and ⁇ T S exceed predetermined thresholds A malicious 2Aphil B shadow and 2B, respectively, the valve 18D is adjusted in order to reduce the variability measurements below the thresholds.
- the sequence of operations carried out by the processor circuit 32 begins with selecting either manual programming or automatic programming and selecting either pre-programmed variability values or previously determined variability values ⁇ lSI and ⁇ T S as a starting set of values for different walking speed ranges.
- the remote control unit referred to in the prior patent application mentioned above is used to send command signals for appropriate valve adjustment and for producing average walking speed values.
- the pre- programmed variability values may be factory set to give a starting point for automatic programming. In some circumstances, if very large variability values are measured, automatic programming may be preceded by manual programming by the prosthetist and reading the previous values of stroke magnitude and stroke duration for each speed range Ti to T 5 stored in EPROM 38 (program element 50).
- step period, stroke magnitude and stroke duration are measured for each walking step (element 54), and for each walking step the value of the step period T is checked against corresponding limit values of the ranges Ti to T 5 to determine whether the step being measured is within the same step period range as the previous step (element 56). If it is not, the new step period range is set (element 58) and the program returns to element 54 to measure and store T, ⁇ lSI and T s for the next walking step.
- step period of the measured step is within the same step period range as the previous step, a counter is incremented (not shown) and the program returns to element 54 to run through the above described sequence again until seven consecutive steps have taken place all within one step period range, as determined by program element 60 in Figure
- the step period range is checked and the step magnitude variability and step duration variability are selected and calculated for the respective seven steps (elements 62 and 64 of the program). Then the stroke magnitude variability is compared with the previous value (element 66). If the variability has increased, it is assumed that the last adjustment of valve 18D (Figure 1) in the relevant step period range was in the wrong direction, and the register setting the direction of valve adjustment is updated to reverse the adjustment direction (element 68) and the previous stroke magnitude variability value is overwritten with the new stroke magnitude variability value (element 70).
- the measured stroke magnitude variability value is compared with a first variability threshold A, (element 72) and if that threshold is exceeded, another comparison is carried out in step 74 to determine whether the variability value exceeds a higher second variability threshold, in this case double the previous threshold, i.e. 2A, (element 74).
- the outcome of program elements 72 and 74 is that if the stroke magnitude variability is below the first threshold A Vogel no valve adjustment occurs. If it is between the first and second thresholds A, and 2Arada the valve is adjusted by half a step of the stepper motor 20 (see Figure 1) in the direction set in the valve adjustment direction register (program element 76). If, however, the stroke magnitude variability is greater than the second threshold 2A warmth the valve is adjusted by one stepper motor step (element 78) in the indicated direction.
- the stroke magnitude variability is within the lower of the two stroke magnitude variability thresholds, as determined by program element 72, the variability of the stroke duration is assessed as a secondary variability measure.
- the stroke duration variability ⁇ Ts is compared against a stroke duration variability threshold B, and, if necessary, against a second stroke duration variability threshold 2B, (in program element 82). Again, depending on the results of these comparisons, the valve 18D is adjusted by half a step or one step in the register- indicated direction, or no adjustment occurs.
- the above-described program elements 54 to 82 form one iteration in an iterative procedure for optimally adjusting valve 18D so as to bring at least the stroke magnitude variability within the lower of its respective threshold (A,). Accordingly, the next time seven steps are completed within the same step period range, the next iteration occurs, and so on until an optimum valve adjustment is obtained. The same process is carried out for other step period ranges. 10
- stroke magnitude variability as the primary variability parameter ensures that reduction of stroke magnitude variability takes precedence over reduction of stroke duration variability.
- stroke duration may be adopted as the primary variability measure, the stroke magnitude variability then becoming the secondary variability measure.
- the above-described program operations can be activated by operating a switch or on detection of a special sequence of movements of the prosthesis, or it may be performed continuously during normal use of the prosthesis.
- the effect of the operation is that adjustment of the control device may be carried out automatically without intervention from a prosthetist. After an initial geometric alignment of the limb and, generally, an approximate adjustment of the control device, the fine adjustment of the control device is a self -teaching automatic procedure.
Abstract
Description
Claims
Priority Applications (5)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
AU32643/99A AU3264399A (en) | 1998-03-04 | 1999-03-03 | Lower limb prosthesis and control unit |
US09/623,790 US6719806B1 (en) | 1998-03-04 | 1999-03-03 | Lower limb prosthesis and control unit |
AT99937863T ATE269683T1 (en) | 1998-03-04 | 1999-03-03 | LEG PROSTHESIS AND CONTROL THEREOF |
DE69918273T DE69918273T2 (en) | 1998-03-04 | 1999-03-03 | LEG INSPECTION AND CONTROL THEREFOR |
EP99937863A EP1059898B1 (en) | 1998-03-04 | 1999-03-03 | Lower limb prosthesis and control unit |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
GBGB9804611.3A GB9804611D0 (en) | 1998-03-04 | 1998-03-04 | Lower limb prosthesis and control unit |
GB9804611.3 | 1998-03-04 |
Publications (1)
Publication Number | Publication Date |
---|---|
WO1999044547A1 true WO1999044547A1 (en) | 1999-09-10 |
Family
ID=10827979
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/GB1999/000640 WO1999044547A1 (en) | 1998-03-04 | 1999-03-03 | Lower limb prosthesis and control unit |
Country Status (7)
Country | Link |
---|---|
US (1) | US6719806B1 (en) |
EP (1) | EP1059898B1 (en) |
AT (1) | ATE269683T1 (en) |
AU (1) | AU3264399A (en) |
DE (1) | DE69918273T2 (en) |
GB (2) | GB9804611D0 (en) |
WO (1) | WO1999044547A1 (en) |
Cited By (10)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO2000038599A1 (en) * | 1998-12-24 | 2000-07-06 | Biedermann Motech Gmbh | Leg prosthesis with an artificial knee joint and method for controlling a leg prosthesis |
US7087090B2 (en) | 2003-11-19 | 2006-08-08 | Bloorview Macmillan Centre | Artificial knee joint |
WO2007110585A2 (en) | 2006-03-24 | 2007-10-04 | Chas. A. Blalchford & Sons Limited | Lower limb prosthesis and control unit |
US7485152B2 (en) | 2005-08-26 | 2009-02-03 | The Ohio Willow Wood Company | Prosthetic leg having electronically controlled prosthetic knee with regenerative braking feature |
DE102008024746A1 (en) * | 2008-05-20 | 2009-12-03 | Otto Bock Healthcare Gmbh | Orthopedic device |
US7691154B2 (en) | 2004-05-07 | 2010-04-06 | össur hf | Systems and methods of controlling pressure within a prosthetic knee |
US7799091B2 (en) | 2000-03-29 | 2010-09-21 | Massachusetts Institute Of Technology | Control system for prosthetic knee |
USRE42903E1 (en) | 2000-01-20 | 2011-11-08 | Massachusetts Institute Of Technology | Electronically controlled prosthetic knee |
US8057550B2 (en) | 2004-02-12 | 2011-11-15 | össur hf. | Transfemoral prosthetic systems and methods for operating the same |
US8801802B2 (en) | 2005-02-16 | 2014-08-12 | össur hf | System and method for data communication with a mechatronic device |
Families Citing this family (41)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6113642A (en) | 1996-06-27 | 2000-09-05 | Mauch, Inc. | Computer controlled hydraulic resistance device for a prosthesis and other apparatus |
DE10000781A1 (en) | 2000-01-11 | 2001-11-29 | Biedermann Motech Gmbh | Device and method for remote maintenance of an electronically controllable prosthesis |
US7736394B2 (en) | 2002-08-22 | 2010-06-15 | Victhom Human Bionics Inc. | Actuated prosthesis for amputees |
AU2003236750B2 (en) | 2002-08-22 | 2006-08-10 | Victhom Human Bionics Inc. | Actuated leg prosthesis for above-knee amputees |
US7101487B2 (en) | 2003-05-02 | 2006-09-05 | Ossur Engineering, Inc. | Magnetorheological fluid compositions and prosthetic knees utilizing same |
US7198071B2 (en) * | 2003-05-02 | 2007-04-03 | Össur Engineering, Inc. | Systems and methods of loading fluid in a prosthetic knee |
US7815689B2 (en) | 2003-11-18 | 2010-10-19 | Victhom Human Bionics Inc. | Instrumented prosthetic foot |
US20050107889A1 (en) | 2003-11-18 | 2005-05-19 | Stephane Bedard | Instrumented prosthetic foot |
EP1718252B1 (en) * | 2004-02-12 | 2018-01-10 | Össur hf | System and method for motion-controlled foot unit |
US7637959B2 (en) | 2004-02-12 | 2009-12-29 | össur hf | Systems and methods for adjusting the angle of a prosthetic ankle based on a measured surface angle |
CN1984623B (en) | 2004-03-10 | 2011-04-13 | 奥瑟Hf公司 | Control system and method for a prosthetic knee |
CA2592042C (en) | 2004-12-22 | 2014-12-16 | Oessur Hf | Systems and methods for processing limb motion |
CN101155557B (en) * | 2005-02-02 | 2012-11-28 | 奥瑟Hf公司 | Sensing systems and methods for monitoring gait dynamics |
CN101151071B (en) | 2005-02-02 | 2010-12-08 | 奥瑟Hf公司 | Prosthetic and orthotic systems usable for rehabilitation |
SE528516C2 (en) | 2005-04-19 | 2006-12-05 | Lisa Gramnaes | Combined active and passive leg prosthesis system and a method for performing a movement cycle with such a system |
EP1909708B2 (en) | 2005-07-29 | 2018-02-28 | Freedom Innovations, LLC | Novel computer controlled prosthetic knee device |
EP1946429B1 (en) * | 2005-08-10 | 2017-06-21 | Bionic Power Inc. | Methods and apparatus for harvesting biomechanical energy |
US8048172B2 (en) | 2005-09-01 | 2011-11-01 | össur hf | Actuator assembly for prosthetic or orthotic joint |
US7531006B2 (en) * | 2005-09-01 | 2009-05-12 | össur hf | Sensing system and method for motion-controlled foot unit |
WO2007027808A2 (en) | 2005-09-01 | 2007-03-08 | össur hf | System and method for determining terrain transitions |
US20100292807A1 (en) | 2007-11-21 | 2010-11-18 | Juan Jose Ochoa Velez | Stabilising Knee Joint for a Lower Limb Prosthesis |
DE102008008284A1 (en) | 2008-02-07 | 2009-08-13 | Otto Bock Healthcare Gmbh | Orthopedic knee joint and method for controlling an orthopedic knee joint |
US9351855B2 (en) | 2008-06-16 | 2016-05-31 | Ekso Bionics, Inc. | Powered lower extremity orthotic and method of operation |
EP2331026B1 (en) * | 2008-06-16 | 2018-11-07 | The Regents of The University of California | Semi-actuated transfemoral prosthetic knee |
US8126736B2 (en) | 2009-01-23 | 2012-02-28 | Warsaw Orthopedic, Inc. | Methods and systems for diagnosing, treating, or tracking spinal disorders |
US8685093B2 (en) | 2009-01-23 | 2014-04-01 | Warsaw Orthopedic, Inc. | Methods and systems for diagnosing, treating, or tracking spinal disorders |
US9017418B2 (en) * | 2009-05-05 | 2015-04-28 | össur hf | Control systems and methods for prosthetic or orthotic devices |
EP2442712B1 (en) * | 2009-06-17 | 2019-09-11 | Össur hf | Feedback control systems and methods for prosthetic or orthotic devices |
US8661893B2 (en) * | 2010-06-29 | 2014-03-04 | Orthosensor Inc. | Prosthetic component having a compliant surface |
US8679186B2 (en) * | 2010-06-29 | 2014-03-25 | Ortho Sensor Inc. | Hermetically sealed prosthetic component and method therefor |
EP2534450B1 (en) * | 2010-02-12 | 2016-04-27 | Freedom Innovations, LLC | Angle measurement device and method |
US9060884B2 (en) | 2011-05-03 | 2015-06-23 | Victhom Human Bionics Inc. | Impedance simulating motion controller for orthotic and prosthetic applications |
US8736087B2 (en) | 2011-09-01 | 2014-05-27 | Bionic Power Inc. | Methods and apparatus for control of biomechanical energy harvesting |
GB201121437D0 (en) | 2011-12-13 | 2012-01-25 | Blatchford & Sons Ltd | A lower limb prothesis |
US9017419B1 (en) | 2012-03-09 | 2015-04-28 | össur hf | Linear actuator |
EP3427702A1 (en) | 2013-02-26 | 2019-01-16 | Össur HF | Prosthetic foot with enhanced stability and elastic energy return |
DE102015106384B4 (en) * | 2015-04-24 | 2017-09-07 | Otto Bock Healthcare Products Gmbh | Method for controlling an attenuation change in an artificial joint |
WO2017049234A1 (en) | 2015-09-18 | 2017-03-23 | Ossur Iceland Ehf | Magnetic locking mechanism for prosthetic or orthotic joints |
US10195099B2 (en) | 2016-01-11 | 2019-02-05 | Bionic Power Inc. | Method and system for intermittently assisting body motion |
GB2576372B (en) | 2018-08-17 | 2023-02-01 | Blatchford Products Ltd | Lower limb prosthesis |
CN113116609B (en) * | 2021-04-19 | 2022-03-25 | 吉林大学 | Knee joint prosthesis with adjustable three-functional shaft |
Citations (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
EP0549855A2 (en) * | 1991-12-05 | 1993-07-07 | Otto Bock Orthopädische Industrie Besitz- und Verwaltungs-Kommanditgesellschaft | System for controlling artificial knee joint action in an above knee prosthesis |
GB2280609A (en) | 1993-06-11 | 1995-02-08 | Blatchford & Sons Ltd | Adaptive prosthesis control system |
WO1996041599A1 (en) * | 1995-06-13 | 1996-12-27 | Otto Bock Orthopädische Industrie Besitz- Und Verwaltungskommanditgesellschaft | Process for controlling the knee brake of a knee prosthesis and thigh prosthesis |
Family Cites Families (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5133774A (en) * | 1988-03-25 | 1992-07-28 | Kabushiki Kaisha Kobe Seiko Sho | Teaching playback swing-phase-controlled above-knee prosthesis |
GB9312131D0 (en) * | 1993-06-11 | 1993-07-28 | Blatchford & Sons Ltd | Prosthesis control system |
US6113642A (en) * | 1996-06-27 | 2000-09-05 | Mauch, Inc. | Computer controlled hydraulic resistance device for a prosthesis and other apparatus |
-
1998
- 1998-03-04 GB GBGB9804611.3A patent/GB9804611D0/en not_active Ceased
-
1999
- 1999-03-03 EP EP99937863A patent/EP1059898B1/en not_active Expired - Lifetime
- 1999-03-03 DE DE69918273T patent/DE69918273T2/en not_active Expired - Lifetime
- 1999-03-03 WO PCT/GB1999/000640 patent/WO1999044547A1/en active IP Right Grant
- 1999-03-03 AU AU32643/99A patent/AU3264399A/en not_active Abandoned
- 1999-03-03 US US09/623,790 patent/US6719806B1/en not_active Expired - Lifetime
- 1999-03-03 AT AT99937863T patent/ATE269683T1/en not_active IP Right Cessation
- 1999-03-03 GB GB9904920A patent/GB2334891B/en not_active Expired - Lifetime
Patent Citations (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
EP0549855A2 (en) * | 1991-12-05 | 1993-07-07 | Otto Bock Orthopädische Industrie Besitz- und Verwaltungs-Kommanditgesellschaft | System for controlling artificial knee joint action in an above knee prosthesis |
GB2280609A (en) | 1993-06-11 | 1995-02-08 | Blatchford & Sons Ltd | Adaptive prosthesis control system |
WO1996041599A1 (en) * | 1995-06-13 | 1996-12-27 | Otto Bock Orthopädische Industrie Besitz- Und Verwaltungskommanditgesellschaft | Process for controlling the knee brake of a knee prosthesis and thigh prosthesis |
Cited By (16)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6755870B1 (en) | 1998-12-24 | 2004-06-29 | Biedermann Motech Gmbh | Leg prosthesis with an artificial knee joint and method for controlling a leg prosthesis |
WO2000038599A1 (en) * | 1998-12-24 | 2000-07-06 | Biedermann Motech Gmbh | Leg prosthesis with an artificial knee joint and method for controlling a leg prosthesis |
USRE42903E1 (en) | 2000-01-20 | 2011-11-08 | Massachusetts Institute Of Technology | Electronically controlled prosthetic knee |
US7799091B2 (en) | 2000-03-29 | 2010-09-21 | Massachusetts Institute Of Technology | Control system for prosthetic knee |
US7087090B2 (en) | 2003-11-19 | 2006-08-08 | Bloorview Macmillan Centre | Artificial knee joint |
US8057550B2 (en) | 2004-02-12 | 2011-11-15 | össur hf. | Transfemoral prosthetic systems and methods for operating the same |
US10195057B2 (en) | 2004-02-12 | 2019-02-05 | össur hf. | Transfemoral prosthetic systems and methods for operating the same |
US7691154B2 (en) | 2004-05-07 | 2010-04-06 | össur hf | Systems and methods of controlling pressure within a prosthetic knee |
US8801802B2 (en) | 2005-02-16 | 2014-08-12 | össur hf | System and method for data communication with a mechatronic device |
US7485152B2 (en) | 2005-08-26 | 2009-02-03 | The Ohio Willow Wood Company | Prosthetic leg having electronically controlled prosthetic knee with regenerative braking feature |
WO2007110585A3 (en) * | 2006-03-24 | 2007-11-22 | Chas A Blalchford & Sons Ltd | Lower limb prosthesis and control unit |
US8403997B2 (en) | 2006-03-24 | 2013-03-26 | Blatchford Products Limited | Lower limb prosthesis and control unit |
WO2007110585A2 (en) | 2006-03-24 | 2007-10-04 | Chas. A. Blalchford & Sons Limited | Lower limb prosthesis and control unit |
US10299943B2 (en) | 2008-03-24 | 2019-05-28 | össur hf | Transfemoral prosthetic systems and methods for operating the same |
US8608678B2 (en) | 2008-05-20 | 2013-12-17 | Otto Bock Healthcare Gmbh | Orthopedic technical device |
DE102008024746A1 (en) * | 2008-05-20 | 2009-12-03 | Otto Bock Healthcare Gmbh | Orthopedic device |
Also Published As
Publication number | Publication date |
---|---|
DE69918273D1 (en) | 2004-07-29 |
ATE269683T1 (en) | 2004-07-15 |
GB9804611D0 (en) | 1998-04-29 |
AU3264399A (en) | 1999-09-20 |
GB9904920D0 (en) | 1999-04-28 |
EP1059898A1 (en) | 2000-12-20 |
GB2334891A (en) | 1999-09-08 |
EP1059898B1 (en) | 2004-06-23 |
GB2334891B (en) | 2002-12-24 |
US6719806B1 (en) | 2004-04-13 |
DE69918273T2 (en) | 2005-07-21 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
EP1059898B1 (en) | Lower limb prosthesis and control unit | |
CA2647117C (en) | Lower limb prosthesis and control unit | |
EP1003442B1 (en) | Prothese de membre inferieur | |
EP1267756B1 (en) | Speed-adaptive and patient-adaptive prosthetic knee | |
US5893891A (en) | Prosthesis control system | |
GB2367753A (en) | A lower limb prosthesis | |
US10695197B2 (en) | Prosthetic ankle and method of controlling same based on weight-shifting | |
EP0549855B1 (en) | System for controlling artificial knee joint action in an above knee prosthesis | |
US6755870B1 (en) | Leg prosthesis with an artificial knee joint and method for controlling a leg prosthesis | |
WO2001017466A2 (en) | A lower limb prosthesis | |
AU2001249759A1 (en) | Speed-adaptive and patient-adaptive prosthetic knee | |
GB2280609A (en) | Adaptive prosthesis control system |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
AK | Designated states |
Kind code of ref document: A1 Designated state(s): AL AM AT AU AZ BA BB BG BR BY CA CH CN CU CZ DE DK EE ES FI GB GD GE GH GM HR HU ID IL IN IS JP KE KG KP KR KZ LC LK LR LS LT LU LV MD MG MK MN MW MX NO NZ PL PT RO RU SD SE SG SI SK SL TJ TM TR TT UA UG US UZ VN YU ZW |
|
AL | Designated countries for regional patents |
Kind code of ref document: A1 Designated state(s): GH GM KE LS MW SD SL SZ UG ZW AM AZ BY KG KZ MD RU TJ TM AT BE CH CY DE DK ES FI FR GB GR IE IT LU MC NL PT SE BF BJ CF CG CI CM GA GN GW ML MR NE SN TD TG |
|
121 | Ep: the epo has been informed by wipo that ep was designated in this application | ||
DFPE | Request for preliminary examination filed prior to expiration of 19th month from priority date (pct application filed before 20040101) | ||
NENP | Non-entry into the national phase |
Ref country code: KR |
|
WWE | Wipo information: entry into national phase |
Ref document number: 1999937863 Country of ref document: EP |
|
WWE | Wipo information: entry into national phase |
Ref document number: 09623790 Country of ref document: US |
|
WWP | Wipo information: published in national office |
Ref document number: 1999937863 Country of ref document: EP |
|
REG | Reference to national code |
Ref country code: DE Ref legal event code: 8642 |
|
WWG | Wipo information: grant in national office |
Ref document number: 1999937863 Country of ref document: EP |